US20050045479A1 - Pumpless microfluidics - Google Patents
Pumpless microfluidics Download PDFInfo
- Publication number
- US20050045479A1 US20050045479A1 US10/821,267 US82126704A US2005045479A1 US 20050045479 A1 US20050045479 A1 US 20050045479A1 US 82126704 A US82126704 A US 82126704A US 2005045479 A1 US2005045479 A1 US 2005045479A1
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- channel
- fluid
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- microfluidic
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- Abandoned
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- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/06—Valves, specific forms thereof
- B01L2400/0688—Valves, specific forms thereof surface tension valves, capillary stop, capillary break
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
- F16K99/00—Subject matter not provided for in other groups of this subclass
- F16K2099/0073—Fabrication methods specifically adapted for microvalves
- F16K2099/0078—Fabrication methods specifically adapted for microvalves using moulding or stamping
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
- F16K99/00—Subject matter not provided for in other groups of this subclass
- F16K2099/0073—Fabrication methods specifically adapted for microvalves
- F16K2099/008—Multi-layer fabrications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N35/00—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor
- G01N2035/00178—Special arrangements of analysers
- G01N2035/00237—Handling microquantities of analyte, e.g. microvalves, capillary networks
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/25—Chemistry: analytical and immunological testing including sample preparation
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/25—Chemistry: analytical and immunological testing including sample preparation
- Y10T436/25625—Dilution
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/25—Chemistry: analytical and immunological testing including sample preparation
- Y10T436/2575—Volumetric liquid transfer
Definitions
- This invention relates generally to microfluidic systems, and, in particular, to a microfluidic device in which the operation is conducted entirely without the benefit of an external fluidic driver.
- Microfluidic devices have become very popular in recent years for performing analytical testing. Using tools developed by the semiconductor industry to miniaturize electronics, it has become possible to fabricate intricate fluid systems which can be inexpensively mass produced. Systems have been developed to perform a variety of analytical techniques for the acquisition and processing of information.
- U.S. Pat. No. 5,716,852 is an example of such a device.
- This patent teaches a microfluidic system for detecting the presence of analyte particles in a sample stream using a laminar flow channel having at least two input channels which provide an indicator stream and a sample stream, where the laminar flow channel has a depth sufficiently small to allow laminar flow of the streams and length sufficient to allow diffusion of particles of the analyte into the indicator stream to form a detection area, and having an outlet out of the channel to form a single mixed stream.
- This device which is known as a T-sensor, allows the movement of different fluidic layers next to each other within a channel without mixing other than by diffusion.
- Microfluidic systems of this type require some type of external fluidic driver, such as piezoelectric pumps, microsyringe pumps, electroosmotic pumps and the like, to operate. It would be desirable, in many situations, to produce a device which is entirely driven by a readily available force, such as gravity, capillary action, absorption in porous materials, chemically induced pressures or vacuums (e.g., by a reaction of water with a drying agent), or by vacuum and pressure generated by simple manual action, rather than by an external fluidic driver requiring a separate power source having moving parts. Such a device could be extremely simple to operate, could be manufactured very inexpensively, and could be used to perform many diagnostic assays using a variety of microfluidic methods.
- external fluidic driver such as piezoelectric pumps, microsyringe pumps, electroosmotic pumps and the like
- a simple cartridge device containing microfluidic channels which perform a variety of analytical techniques for the acquisition of information without the use of any electrical or mechanical driving forces applied to the cartridge.
- the cartridge may be constructed from a single material, such as plastic, by conventional manufacturing methods, such as injection molding, to create a low cost device which can be discarded after a single use.
- Inherently available forces such as gravity, hydrostatic pressure, capillary force, absorptive force manually generated pressure, or vacuum, move the fluids through the microfluidic channels to accomplish the desired analytical analyses.
- Other applications for this technology include toys and advertising devices.
- FIG. 1 is a plan view of a microfluidic device manufactured according to the present invention.
- FIG. 2 is a plan view depicting an alternative embodiment of the cartridge of FIG. 1 ;
- FIG. 3 is another alternative embodiment of the cartridge of the present invention which is driven by absorption
- FIG. 4 is a sectional view taken along lines 4 - 4 of FIG. 3 ;
- FIG. 5 is another alternative embodiment of the cartridge of the present invention which is driven by capillary action
- FIG. 6 is another alternative embodiment of the cartridge of the present invention which is driven by hydrostatic pressure
- FIG. 7 is another embodiment of the cartridge of the present invention which is driven by aspiration within the cartridge itself;
- FIG. 8 is another embodiment of the cartridge of the present invention which is driven by a chemical process or a pump from within the cartridge;
- FIG. 9 is another embodiment of the cartridge shown in FIG. 6 having an H-Filter within the cartridge
- FIG. 10 is a graph showing the relationship between hydrostatic pressure and Reynolds number for a typical microfluidic mixing structure
- FIG. 11 is another embodiment of the cartridge of FIG. 3 which is driven by absorption
- FIG. 12 is an enlarged view of an alternative embodiment of an absorption material for use in the present invention.
- FIG. 13 is another embodiment of the cartridge of the present invention exhibiting improved fluid flow within the cartridge
- FIG. 14 is an enlarged view of a portion of the cartridge of FIG. 13 ;
- FIG. 15 is a graphic representation of a T-Sensor for use in the present invention.
- FIG. 16 is a graphic representation similar to FIG. 15 showing a T-Sensor using different analytes
- FIG. 17 is a graphic representation of a T-Sensor using a readout device according to the present invention.
- FIG. 18 is a fragmentary view of a microfluidic channel joining two reservoirs in a Y-junction constructed according to the present invention.
- Cartridge 10 is preferably constructed from a single material, such as plastic, using a method such as injection molding, and is approximately the size and thickness of a typical credit card.
- Cartridge 10 Located within cartridge 10 are several flow channel systems 12 , preferably comprising T-Sensors which are described in detail in U.S. Pat. No. 5,716,852, which disclosure incorporated by reference herein.
- Each T-Sensor 12 consists of a first sample channel 14 , a second sample channel 16 , a common channel 18 , and a terminating storage chamber or reservoir 20 .
- a circular input port 14 a , 16 a respectively At the end of each channel 14 , 16 opposite common channel 18 is located a circular input port 14 a , 16 a respectively, where droplets of reagents and samples can be placed for analysis.
- T-Sensor 12 allows the movement of different fluidic layers next to each other within channel 18 without mixing other than diffusion, as fluids generally show laminar behavior within microfluidic channels.
- a sample solution placed in port 14 a passes through channel 14 and an indicator solution placed in port 16 a passes through channel 16 , and the streams from channels 14 , 16 merge in common channel 18 and flow next to each other until they exit into reservoir 20 .
- Smaller particles such as ions or small proteins diffuse rapidly across the fluid boundaries within channel 18 , whereas larger molecules diffuse more slowly. Large particles, such as blood cells, show no significant diffusion within the time the two flow streams are in contact.
- An interface zone is formed between the fluid layers.
- the signal strength of a particular optical or electrochemical property, such as fluorescence intensity of the interface zone is a function of the concentration of the analyte.
- it is sometimes desirable to add a third stream to T-Sensor 12 with one channel containing a reference stream for analysis purposes. This is described in detail in U.S. Pat. No. 5,948,684, which issued Sep. 7, 1999.
- T-Sensor 12 Manually operated microfluidic devices such as T-Sensor 12 can be used to qualitatively or semi-quantitatively determine analyte concentrations.
- a practical use may be the determination of several parameters directly in whole blood.
- a color change in the diffusion zone of a T-Sensor detection channel can provide qualitative information about the presence of an analyte.
- This method can be made semi-quantitative by providing a comparator color chart with which to compare the color of the diffusion zone. This method would work somewhat similar to a paper test strip, but with much better control and reproducibility.
- long term monitoring functions can be accomplished by placing such a device in line with a sample feed. With a T-Sensor, assays can be performed directly with whole blood, whereas paperstrip readings can be affected by the color and consistency of whole blood.
- the accuracy of this method can be enhanced by combining the device with a readout system which may consist of an absorbance, fluorescence, chemiluminescence, light scatter, or turbidity detector placed so that the detector can observe an optically detectable change which is caused by the presence or absence of a sample analyte or particle in the detection channel.
- a readout system which may consist of an absorbance, fluorescence, chemiluminescence, light scatter, or turbidity detector placed so that the detector can observe an optically detectable change which is caused by the presence or absence of a sample analyte or particle in the detection channel.
- electrodes can be placed within the device to observe electrochemically observable changes caused by the presence or absence of a sample analyte or particle in the in the detection channel.
- One embodiment of this device is a disposable cartridge combined with a mass market digital camera-like detector system: a flash would illuminate the sensor area, and any type of optically detectable signal would be interpreted by image processing software and yield a chemical concentration or count output.
- FIG. 2 shows an alternative embodiment for cartridge 10 of FIG. 1 . Note that in the various embodiments, similar elements have been given similar numerals.
- Cartridge 10 a contains four separate T-Sensor circuits 12 a , 12 b , 12 c , 12 d . These T-Sensors include common channels 16 a , 16 b , 16 c , 16 d having different configurations.
- FIGS. 1 and 2 The driving force for operating cartridges such as those shown in FIGS. 1 and 2 is generally supplied from an external source.
- U.S. patent application Ser. No. 09/080,691 which was filed on May 18, 1998, the disclosure of which is hereby incorporated by reference in its entirety, is an example of a device which requires external motive forces to operate properly.
- Various syringe pumps located external to the cartridge are coupled to the device for operation.
- FIG. 3 shows a device which uses an internal force to drive the circuitry.
- FIG. 3 there is shown a T-Sensor 12 within cartridge 10 b , substantially similar to that taught in FIG. 1 .
- Channels 14 , 16 intersect to form common channel 18 which terminates in reservoir 20 .
- Input ports 14 a , 16 a are connected to channels 14 , 16 respectively at the ends opposite channel 18 .
- a porous absorbent material 30 is positioned within channels 14 , 16 , 18 and reservoir 20 of cartridge 10 b , as can be clearly seen in FIG. 4 .
- a liquid sample of reagent is applied to port 14 a while a liquid sample of a specimen is applied to port 16 a .
- Material 30 acts to propel the liquids through channels 14 , 16 , 18 into reservoir 20 .
- Material 30 is preferably an absorbent hydrophilic substance such as cellulose, calcium chloride, calcium sulfate, or silica gel.
- FIG. 11 shows another embodiment of a cartridge using the absorption principles of the present invention.
- cartridge 10 b uses a T-Sensor like device 12 having three input ports 14 a , 15 a , 16 a coupled to channels 14 , 15 , 16 which converge to form common channel 18 .
- Channel 18 terminates at a reservoir 32 which contains a circular absorbent material 33 .
- Channel 18 is connected to reservoir 32 , and thus material 33 , by a series of small apertures 34 , which, in the present embodiment, allow a fluid traveling within channel 18 to initially reach the center of circular absorbent material 32 .
- material 33 acts to propel fluid through channels 14 , 15 , 16 and common channel into reservoir 32 .
- the absorption begins at the center of material 33 , and expands exponentially the amount of absorption front as the absorption spot expands.
- the flow speed of the fluid absorbed by material 33 can be controlled as desired.
- FIG. 12 shows an enlarged section of a cartridge using the absorption principles shown in FIG. 11 .
- common channel 18 terminates in a triangular section 36 of absorbent material.
- material 36 As fluid travels through channel 18 in the direction shown by arrow A, it reaches material 36 , and since it is triangularly shaped, the length of the diffusion front is increased as diffusion progresses, thereby compensating for an increase in fluid resistance in material 36 as more fluid must pass through already wetted absorbent material.
- Other geometries which can be used in the present invention include hyperbolically expanding triangular shapes.
- Different shapes may not only be used for both keeping the flow speed constant, but also for increasing or decreasing the flow speed, or for cyclically varying the flow speed.
- a sinusoidal expanding “triangular” shape can be used to keep the average flow speed constant, but let it vary periodically.
- the movement of fluids through cartridge 10 b can be enhanced by means of a surface treatment on the walls of channels 14 , 15 , 16 and 18 formed by contacting the surface with low-pressure plasma.
- other features which enhance fluid flow such as capillary forces and gravity feed, can be employed to assist this method.
- Another method available for use in cartridge 10 b of FIG. 11 is driven by evaporation, where absorbent material 33 is not used, and reservoir 32 is exposed to the atmosphere outside cartridge 10 b , where a portion of the fluid from channel 18 evaporates. If the area of fluid that is exposed to atmosphere at the outlet is larger than that at the inlet, then fluid movement will occur in principle. Alternatively, one or both of the outlet or inlet can be cooled or heated, thereby controlling the evaporation rate and, thus, the fluid flow rate and direction, to maintain a constant flow rate or to vary the rate.
- the device in FIG. 11 can be operated beyond the time at which the absorptive capacity of the absorbent pad is exhausted.
- Reservoir 32 has a relatively large surface area, causing the evaporation of fluid at a higher rate than the combined areas of inlet reservoirs 14 a , 15 a , and 16 a . This creates a motive force, driving the fluid contained in cartridge 10 b towards the apertures 34 .
- material 33 is not required for the function of this device.
- the movement of fluid through a microfluidic cartridge by differential evaporation at the inlet and outlet reservoirs is, provided that all evaporation areas are kept at the same temperature, only a function of the surface area of these evaporation areas. If the surfaces are liquid-filled, then the actual area differences determine the force driving the fluid movement. If the surfaces are a wetted porous material such as a filter paper, then the surface roughness also increases the effective surface area. The rougher a surface is, the more “evaporative force” it creates.
- the differential “evaporative force” can be enhanced by keeping the different evaporative areas at different temperatures, as evaporation is enhanced by increased temperature. For example, an inlet area at a low temperature, and an outlet area of the same size as the inlet area, but at a higher temperature, would create fluid movement towards the outlet.
- a magnetic material can be placed within reservoir 20 , and the liquids applied to ports 14 a , 16 a comprise ferrofluids which would be propelled through channels 14 , 16 , 18 by magnetic forces into reservoir 20 .
- ferrofluids could also be used in combination with reagents and specimen samples to either push or pull these fluids through T-Sensor 12 by magnetic forces.
- FIG. 5 shows another alternative design for operating the T-Sensor of FIG. 1 .
- a liquid sample of reagent is applied to port 14 a of cartridge 10 c while a liquid sample of specimen is applied to port 16 a .
- Channels 14 , 16 , and 18 are sized such that capillary action draws the reagent and specimen through channels 14 , 16 and 18 of T-Sensor 12 into terminating reservoir 20 .
- Channels 14 , 16 , and 18 preferably have dimensions between 10 nanometers and 500 micrometers in width, which act to create capillary action to power T-Sensor 12 .
- FIG. 6 is still another alternative embodiment for T-Sensor operation.
- T-Sensor 12 includes a first pressure head 40 for receiving a reagent sample and a second pressure head 42 for receiving a specimen sample.
- the cartridge is placed vertically and a sample of reagent is introduced into channel 14 via head 40 and a sample of specimen introduced into channel 16 via head 42 .
- the hydrostatic pressure present by virtue of the orientation of cartridge 10 d drives the liquids through channel 18 of T-Sensor 12 and into reservoir 20 .
- the velocity at which the liquids travel through cartridge 10 d can be varied by tilting the cartridge from the vertical position.
- cartridge 10 d includes pressure heads 40 and 42 which are coupled to channels 14 and 16 respectively, which flow into common channel 18 .
- Channel 18 eventually connects to a reservoir 20 , which is preferably vented to the atmosphere external to cartridge 10 d via a venting aperture 21 .
- Connection 22 between channel 18 and reservoir 20 is a right angle bend which is located at some distance from bottom wall section 23 and reservoir 20 .
- FIG. 14 is an enlarged view of the connection between channel 18 and reservoir 20 . While the horizontal dimension of the channel mouth at connection 22 may be narrow or wide, vertical dimension 24 must be large enough that the surface tension of a liquid 25 flowing with channel 18 is inadequate to support a liquid drop. if this requirement is fulfilled within the structure of cartridge 10 d , the liquid 25 entering reservoir forms a thin stream as shown at 26 from the bottom of connection 22 and flows down the wall 27 of reservoir 20 . By using this structure, pressure oscillations in channel 18 that would occur as drops form and fall within reservoir 20 is avoided, thus ensuring a smooth liquid flow.
- Hydrostatically driven microfluidic circuits use gravity as their driving force.
- the pressure generated is a function of the difference in inlet and outlet liquid height level. This pressure is a constant for a given height difference, and generates a fluid flow in the microfluidic circuit.
- Flow speed and flow ratios for a given pressure are largely a function of the fluid resistance in these microchannels, and of the viscosity of the solutions. For example, in a given T-Sensor, the fluid flow ratio between the two fluids will depend on the viscosity ratio of the two fluids. Blood has a viscosity about 3-4.5 times greater than that of aqueous solutions.
- One method to compensate for a change in flow speed due to a change in viscosity is to include a small “metering bubble” in the inlet channels. The time it takes to fill this bubble is proportional to the flow speed of each solution, which again is proportional to the viscosity of each solution.
- hydrostatic pressure is a very constant source of power for microfluidic structures, it may be necessary at times for some types of structures to overcome some initial surface effects while filling a cartridge prior to allowing gravity or capillary forces to keep the flow constant and well controlled.
- a variety of methods for “jump-starting” the flow can be used: tapping on the inlets, using a syringe to either aspirate or press fluid into the disposable, using a “bubble pump”, or a variety of other processes.
- Microfluidic cartridges can also be surface-treated (for example, by a so-called Oxygen Plasma process) to create surfaces that can be more easily wetted by aqueous solutions. Such cartridges generally do not need to be “jump-started”, as the capillary forces draw fluids into these cartridges autonomously. By selective surface treatment, some areas of the cartridge can be filled, while others can create so-called surface tension valves, which require a certain amount of pressure to overcome before they wet.
- FIG. 7 An alternate embodiment of the cartridge of FIG. 6 is shown in FIG. 7 .
- a vent passage 50 is connected to reservoir 20 .
- Vent passage 50 includes a compressible aspiration bubble pump 52 and a closure means 54 .
- aspiration bubble 52 is depressed while a reagent sample and a specimen sample are introduced into pressure heads 40 , 42 .
- closure means 54 is activated to seal vent passage 50 from atmosphere. Bubble 52 is then released causing the reagent and specimen to enter T-Sensor 12 via channels 14 , 16 and 18 and into reservoir 20 .
- FIG. 8 shows yet another version of the cartridge of the present invention.
- Cartridge 10 f contains a compressible pressure bubble 60 which is connected to parts 14 a and 16 a via passages 62 , 64 respectively, while vent passage 50 connects reservoir 20 to atmosphere.
- T-Sensor 12 in cartridge 10 f operates as follows: bubble 60 is depressed, forcing air through passages 62 , 64 , and consequently causing reagent 14 a and specimen in port 16 a to enter T-Sensor 12 via channels 14 , 16 and 18 and into reservoir 20 .
- Bubble 60 can alternatively contain a liquid in equilibrium with its gas phase; some liquids, such as alcohol, acetone, methanol, have a vapor pressure high enough at room temperature to provide a constant pressure source to drive liquids through T-Sensor 12 .
- the pressure source will only cease once all the liquid in bubble 60 has been converted to the gas phase; until then, pressure will be constant, and only a function of temperature.
- H-Filter Another type of microfluidic device which can be readily adapted to manual operation is the H-Filter.
- the H-Filter structure is described in detail in U.S. Pat. No. 5,932,100, the disclosure of which is hereby incorporated by reference.
- Manually operated H-Filters can be used to separate components from particulate-laden samples such as whole blood, or to manufacture small quantities of chemicals.
- FIG. 9 shows a cartridge similar to FIG. 6 embodying the present invention in the form of an H-Filter.
- Cartridge 10 g contains a first pressure head 40 for receiving a reagent sample and a second pressure head 42 for receiving a specimen sample.
- An H-Filter 70 is coupled to pressure heads 40 , 42 via channels 14 , 16 respectively.
- H-Filter 70 consists of a channel 72 which connects channels 14 , 16 to a pair of separate reservoirs 74 , 76 , which are connected only through a common vent 80 .
- channel 72 of H-Filter 70 follows a serpentine path which assists in creating turbulence to enhance mixing; however, channel 72 can be straight, such as channel 16 c shown in T-Sensor 12 c in FIG. 2 .
- a sample such as whole blood
- an acceptor reagent such as water or saline
- Two parallel laminar streams will flow through channel 72 as the liquids travel from channels 14 , 16 . Smaller components of the sample stream will diffuse into the acceptor stream.
- the two parallel flows are then split up into separate reservoirs 74 , 76 at the end of H-Filter 70 .
- Reservoir 74 will then contain a sample solution with a reduced concentration of the extracted component, while reservoir 76 contains the acceptor reagent containing the extracted reagent at a level of some fraction of its original concentration in the sample.
- the contents of both reservoirs 74 , 76 can then be harvested from cartridge 10 g for future use, or be processed through further integrated microfluidic structures.
- reagents can be placed in inlet reservoirs, and sealed with a membrane, tape, or the like. Prior to the measurement, the user fills the sample inlet reservoir, and then removes the reagent seal. This process allows the reagents to start flowing down the channel.
- Alternative sealing methods may be surface-tension controlled orifices which require a certain initial pressure to overcome the surface effects, and to start flowing, or other types of manual or mechanical valves.
- fluids can be pumped in a closed circuit for a period of time. This may be advantageous when extracting or washing samples or reagents, and multiple passes through a microfluidic structure would increase the yield.
- Mixing solutions in manually driven microfluidic circuits can be either diffusion-based in a laminar channel (as in H-Filters and T-Sensors), or quasi-turbulent.
- Several structures can be used to mix solutions in a quasi-turbulent fashion. Generally, such structures consist of a succession of corners, edges, zig-zag channels, or other features which increase the likelihood that laminar recirculation or turbulence can be generated in microchannels at the flow speeds available with a manually driven microfluidic circuit.
- FIG. 10 shows the relationship between hydrostatic pressure and Reynolds number for a typical microfluidic mixing structure. A Reynolds number of 10 is usually sufficient to induce mixing. Turbulent or quasi-turbulent mixing is required for relatively large particles (Molecular weight of 1000 KD or more). Alternatively, bubble pumps can generate enough pressure to turbulently mix solutions in most microfluidic structures.
- antibody-antigen complexes may either sediment into a microfluidic reservoir for detection or further processing, or they may form particles that intentionally get stuck in small microfluidic features such as orifices.
- the presence or absence of these complexes in particular parts of the microstructures can serve as an indicator for the presence, absence, or quantity of an analyte. This could be used to develop a method for blood typing.
- FIGS. 15-17 A simple detection method for analyzing the results of an assay performed is a microfluidic format according to the present invention is shown in FIGS. 15-17 .
- a basic T-Sensor device 12 is shown having an indicator port 14 a and an analyte port 16 a .
- Port 14 a is connected to main channel 18 by a sample channel 14
- port 16 a is connected to channel 18 by an analyte channel 16 a .
- a high concentration analyte is loaded into port 16
- T-Sensor 12 is operated with an indicator solution within port 14 , a diffusion pattern forms as shown at 90 .
- a low concentration analyte is loaded into port 16 , and a different diffusion pattern 92 is generated.
- channel 18 At some point along channel 18 , the reaction between the analyte and indicator will become sufficiently intense to be seen visually. This point in channel 18 , which is located some distance from channels 14 a and 16 a , will correlate with a particular concentration of analyte within channel 18 .
- Optical aids such as a magnifying lens, colored filter layer, or slit may aid on the manual visual interpretation of the concentration.
- FIG. 17 An example of a device for simple quantitation of a microfluidic device which requires no external instruments is shown in FIG. 17 .
- a convoluted T-Sensor 12 e having ports 14 , 16 and channels 14 a , 16 a contains a main channel 18 a upon which a viewing window 100 has been inserted.
- a chart 102 is placed near T-Sensor 12 e which contains indicia representative of different concentrations of the desired analyte.
- quantitation is achieved by interpreting the point at which a visible reaction has occurred at the interface between the sample and indicator.
- the only portion of Channel 18 visible is seen through viewing window 100 .
- the analyte may be at a 4+ to 5+ amount (1+ being low, 10+ being high) because in the 6+view area of window 100 , there is barely an reaction visible.
- This embodiment is aimed at providing a quantitative assessment of analyte concentration in a format that is compatible with manual performance and visual readout.
- This format is particularly appropriate for use with kinetic assays—in which product builds up with time—since time in a microfluidic channel corresponds to geographic distance.
- kinetic assays are enzyme assays, and some slow finding reactions, such as some antibody-antigen reaction.
- this technique may also work with “fast” reactions, because visual interpretation incorporates both intensity of color and “thickness” of color at the interface.
- FIG. 18 shows a microfluidic device according to the present invention which joins two fluid streams in a manner which prevents the formation of air bubbles within the channels that may hamper the performance of the device.
- a pair of reservoirs 14 a , 16 a are coupled to a main microfluidic outlet channel 18 by a pair of inlet channels 14 , 16 respectively.
- channel 18 is tapered such that it is wider at section 18 a where it connects to channels 14 , 16 .
- Channel 14 connects to reservoir 14 a at 110
- channel 16 connects to reservoir 16 a at 112 .
- the outlet channel 18 must be large enough to contain the volume of inlet channel 14 from reservoir 14 a without trapping the air in channel 16 .
- the pressure differential between the pressure in outlet channel 18 and the pressure at 110 which is due to the fluid resistance to flow within channel 14
- the pressure differential between the pressure in outlet channel 18 and the pressure at 112 which is due to the surface tension of the gas-liquid interface at 112 . This is accomplished by narrowing the width of channel 16 as needed for the surface tension characteristic of the liquid and gas pair.
- valves are based on the difference in resistance contained in unwetted orifice as compared to a wetted orifice. These valves are considered “single use” valves, as once they are wetted, they behave essentially like a low resistance flow channel (dynamic resistance); however, these valves present enough resistance (static resistance) to block the fluid flow, even if some force is applied to them such as pressure, capillary forces, or hydrostatic pressure. Once this static force is overcome by a “breaking force,” fluid will flow through the valve.
- Resistance of the inlet channels 14 , 16 is only dynamic resistance. The more the inlet channels are filled, the higher the resistance (provided that there are no capillary forces to drive fluids through these inlet channels).
- One method of improving the reliability of surface tension valves would be to provide multiple redundant surface tension valves in parallel rather than a single valve. Although the multiple valves will vary statistically in resistance, but the average of the group will be close to that of a single valve. For example, by placing multiple small orifices between two channels, the same approximate surface tension can be achieved each time.
- FIG. 11 shows the use of multiple orifices within a channel to exhibit this principle.
- a cartridge containing a microfluidic device as described can be used as science kits, such as a miniature chemical laboratory, for educational purposes.
- science kits such as a miniature chemical laboratory
- Another use could be as a novelty device that uses fluid flow to visualize specific patterns, such as company logos, names, signatures, and the like on a small plastic card roughly the size of a standard credit card.
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Abstract
A microfluidic device which operates without the need for an external power source. The device includes a body structure, at least one microscale channel within the structure, a port for introducing fluid into the channel, and a power source internal to the structure for propelling the fluid through the channel. Various structures are described which embody the invention.
Description
- This patent application is a continuation of U.S. patent application Ser. No. 09/684,094 filed Oct. 6, 2000 (now allowed); which application is a continuation-in-part of U.S. patent application Ser. No. 09/415,404, filed Oct. 8, 1999 (now abandoned) and which also claims the benefit of U.S. Provisional Patent Application Ser. No. 60/213,865 filed Jun. 23, 2000, which applications are incorporated herein in their entireties by reference.
- 1. Field of Invention
- This invention relates generally to microfluidic systems, and, in particular, to a microfluidic device in which the operation is conducted entirely without the benefit of an external fluidic driver.
- 2. Description of the Related Art
- Microfluidic devices have become very popular in recent years for performing analytical testing. Using tools developed by the semiconductor industry to miniaturize electronics, it has become possible to fabricate intricate fluid systems which can be inexpensively mass produced. Systems have been developed to perform a variety of analytical techniques for the acquisition and processing of information.
- U.S. Pat. No. 5,716,852 is an example of such a device. This patent teaches a microfluidic system for detecting the presence of analyte particles in a sample stream using a laminar flow channel having at least two input channels which provide an indicator stream and a sample stream, where the laminar flow channel has a depth sufficiently small to allow laminar flow of the streams and length sufficient to allow diffusion of particles of the analyte into the indicator stream to form a detection area, and having an outlet out of the channel to form a single mixed stream. This device, which is known as a T-sensor, allows the movement of different fluidic layers next to each other within a channel without mixing other than by diffusion.
- Microfluidic systems of this type require some type of external fluidic driver, such as piezoelectric pumps, microsyringe pumps, electroosmotic pumps and the like, to operate. It would be desirable, in many situations, to produce a device which is entirely driven by a readily available force, such as gravity, capillary action, absorption in porous materials, chemically induced pressures or vacuums (e.g., by a reaction of water with a drying agent), or by vacuum and pressure generated by simple manual action, rather than by an external fluidic driver requiring a separate power source having moving parts. Such a device could be extremely simple to operate, could be manufactured very inexpensively, and could be used to perform many diagnostic assays using a variety of microfluidic methods.
- Accordingly, it is an object of the present invention to provide a microfluidic device which can be operating without a fluid driver that requires a power source.
- It is a further object of the present invention to provide a low cost disposable qualitative assay which can be adapted to medical or environmental uses, among others.
- It is still a further object of the present invention to provide a simple microfluidic system which can perform analytical functions without the necessity of an external electrical or mechanical fluid driver system.
- These and other objects are accomplished in the present invention by a simple cartridge device containing microfluidic channels which perform a variety of analytical techniques for the acquisition of information without the use of any electrical or mechanical driving forces applied to the cartridge. The cartridge may be constructed from a single material, such as plastic, by conventional manufacturing methods, such as injection molding, to create a low cost device which can be discarded after a single use. Inherently available forces such as gravity, hydrostatic pressure, capillary force, absorptive force manually generated pressure, or vacuum, move the fluids through the microfluidic channels to accomplish the desired analytical analyses. Other applications for this technology include toys and advertising devices.
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FIG. 1 is a plan view of a microfluidic device manufactured according to the present invention; -
FIG. 2 is a plan view depicting an alternative embodiment of the cartridge ofFIG. 1 ; -
FIG. 3 is another alternative embodiment of the cartridge of the present invention which is driven by absorption; -
FIG. 4 is a sectional view taken along lines 4-4 ofFIG. 3 ; -
FIG. 5 is another alternative embodiment of the cartridge of the present invention which is driven by capillary action; -
FIG. 6 is another alternative embodiment of the cartridge of the present invention which is driven by hydrostatic pressure; -
FIG. 7 is another embodiment of the cartridge of the present invention which is driven by aspiration within the cartridge itself; -
FIG. 8 is another embodiment of the cartridge of the present invention which is driven by a chemical process or a pump from within the cartridge; -
FIG. 9 is another embodiment of the cartridge shown inFIG. 6 having an H-Filter within the cartridge; -
FIG. 10 is a graph showing the relationship between hydrostatic pressure and Reynolds number for a typical microfluidic mixing structure; -
FIG. 11 is another embodiment of the cartridge ofFIG. 3 which is driven by absorption; -
FIG. 12 is an enlarged view of an alternative embodiment of an absorption material for use in the present invention; -
FIG. 13 is another embodiment of the cartridge of the present invention exhibiting improved fluid flow within the cartridge; -
FIG. 14 is an enlarged view of a portion of the cartridge ofFIG. 13 ; -
FIG. 15 is a graphic representation of a T-Sensor for use in the present invention; -
FIG. 16 is a graphic representation similar toFIG. 15 showing a T-Sensor using different analytes; -
FIG. 17 is a graphic representation of a T-Sensor using a readout device according to the present invention; and -
FIG. 18 is a fragmentary view of a microfluidic channel joining two reservoirs in a Y-junction constructed according to the present invention. - Referring now to
FIG. 1 , there is shown a cartridge generally indicated at 10 containing the elements of the present invention. Note that like parts are given like reference numerals in the embodiments contained in the present application. Cartridge 10 is preferably constructed from a single material, such as plastic, using a method such as injection molding, and is approximately the size and thickness of a typical credit card. Located withincartridge 10 are severalflow channel systems 12, preferably comprising T-Sensors which are described in detail in U.S. Pat. No. 5,716,852, which disclosure incorporated by reference herein. Each T-Sensor 12 consists of afirst sample channel 14, asecond sample channel 16, acommon channel 18, and a terminating storage chamber orreservoir 20. At the end of eachchannel common channel 18 is located acircular input port - In operation, T-
Sensor 12 allows the movement of different fluidic layers next to each other withinchannel 18 without mixing other than diffusion, as fluids generally show laminar behavior within microfluidic channels. A sample solution placed inport 14 a passes throughchannel 14 and an indicator solution placed inport 16 a passes throughchannel 16, and the streams fromchannels common channel 18 and flow next to each other until they exit intoreservoir 20. Smaller particles such as ions or small proteins diffuse rapidly across the fluid boundaries withinchannel 18, whereas larger molecules diffuse more slowly. Large particles, such as blood cells, show no significant diffusion within the time the two flow streams are in contact. An interface zone is formed between the fluid layers. The signal strength of a particular optical or electrochemical property, such as fluorescence intensity of the interface zone is a function of the concentration of the analyte. In addition, it is sometimes desirable to add a third stream to T-Sensor 12, with one channel containing a reference stream for analysis purposes. This is described in detail in U.S. Pat. No. 5,948,684, which issued Sep. 7, 1999. - Manually operated microfluidic devices such as T-
Sensor 12 can be used to qualitatively or semi-quantitatively determine analyte concentrations. A practical use may be the determination of several parameters directly in whole blood. A color change in the diffusion zone of a T-Sensor detection channel can provide qualitative information about the presence of an analyte. This method can be made semi-quantitative by providing a comparator color chart with which to compare the color of the diffusion zone. This method would work somewhat similar to a paper test strip, but with much better control and reproducibility. In addition, long term monitoring functions can be accomplished by placing such a device in line with a sample feed. With a T-Sensor, assays can be performed directly with whole blood, whereas paperstrip readings can be affected by the color and consistency of whole blood. - The accuracy of this method can be enhanced by combining the device with a readout system which may consist of an absorbance, fluorescence, chemiluminescence, light scatter, or turbidity detector placed so that the detector can observe an optically detectable change which is caused by the presence or absence of a sample analyte or particle in the detection channel. Alternatively, electrodes can be placed within the device to observe electrochemically observable changes caused by the presence or absence of a sample analyte or particle in the in the detection channel.
- One embodiment of this device is a disposable cartridge combined with a mass market digital camera-like detector system: a flash would illuminate the sensor area, and any type of optically detectable signal would be interpreted by image processing software and yield a chemical concentration or count output.
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FIG. 2 shows an alternative embodiment forcartridge 10 ofFIG. 1 . Note that in the various embodiments, similar elements have been given similar numerals.Cartridge 10 a contains four separate T-Sensor circuits common channels - The driving force for operating cartridges such as those shown in
FIGS. 1 and 2 is generally supplied from an external source. U.S. patent application Ser. No. 09/080,691, which was filed on May 18, 1998, the disclosure of which is hereby incorporated by reference in its entirety, is an example of a device which requires external motive forces to operate properly. Various syringe pumps located external to the cartridge are coupled to the device for operation.FIG. 3 , however, shows a device which uses an internal force to drive the circuitry. - Turning now to
FIG. 3 , there is shown a T-Sensor 12 withincartridge 10 b, substantially similar to that taught inFIG. 1 .Channels common channel 18 which terminates inreservoir 20.Input ports channels channel 18. A porousabsorbent material 30 is positioned withinchannels reservoir 20 ofcartridge 10 b, as can be clearly seen inFIG. 4 . To operate the T-Sensor ofFIG. 3 , a liquid sample of reagent is applied to port 14 a while a liquid sample of a specimen is applied to port 16 a.Material 30 acts to propel the liquids throughchannels reservoir 20.Material 30 is preferably an absorbent hydrophilic substance such as cellulose, calcium chloride, calcium sulfate, or silica gel. -
FIG. 11 shows another embodiment of a cartridge using the absorption principles of the present invention. Referring now toFIG. 11 ,cartridge 10 b uses a T-Sensor likedevice 12 having threeinput ports channels common channel 18.Channel 18 terminates at areservoir 32 which contains a circularabsorbent material 33.Channel 18 is connected toreservoir 32, and thusmaterial 33, by a series ofsmall apertures 34, which, in the present embodiment, allow a fluid traveling withinchannel 18 to initially reach the center of circularabsorbent material 32. As fluid fromchannel 18reaches material 33,material 33 acts to propel fluid throughchannels reservoir 32. In this embodiment, fluid exits fromapertures 34 onto the center ofmaterial 33 and travels radially at a constant speed toward the outer circumference ofcircular material 33, thus providing a constant flow speed withinchannel 18 as the fluid is absorbed bymaterial 33. The absorption begins at the center ofmaterial 33, and expands exponentially the amount of absorption front as the absorption spot expands. By varying the shape, geometry, and directional preference ofabsorbent pad 33, the flow speed of the fluid absorbed bymaterial 33 can be controlled as desired. -
FIG. 12 shows an enlarged section of a cartridge using the absorption principles shown inFIG. 11 . In this embodiment,common channel 18 terminates in atriangular section 36 of absorbent material. As fluid travels throughchannel 18 in the direction shown by arrow A, it reachesmaterial 36, and since it is triangularly shaped, the length of the diffusion front is increased as diffusion progresses, thereby compensating for an increase in fluid resistance inmaterial 36 as more fluid must pass through already wetted absorbent material. Other geometries which can be used in the present invention include hyperbolically expanding triangular shapes. - Different shapes may not only be used for both keeping the flow speed constant, but also for increasing or decreasing the flow speed, or for cyclically varying the flow speed. For example, a sinusoidal expanding “triangular” shape can be used to keep the average flow speed constant, but let it vary periodically.
- The movement of fluids through
cartridge 10 b can be enhanced by means of a surface treatment on the walls ofchannels - Another method available for use in
cartridge 10 b ofFIG. 11 is driven by evaporation, whereabsorbent material 33 is not used, andreservoir 32 is exposed to the atmosphere outsidecartridge 10 b, where a portion of the fluid fromchannel 18 evaporates. If the area of fluid that is exposed to atmosphere at the outlet is larger than that at the inlet, then fluid movement will occur in principle. Alternatively, one or both of the outlet or inlet can be cooled or heated, thereby controlling the evaporation rate and, thus, the fluid flow rate and direction, to maintain a constant flow rate or to vary the rate. - According to this method, the device in
FIG. 11 can be operated beyond the time at which the absorptive capacity of the absorbent pad is exhausted.Reservoir 32 has a relatively large surface area, causing the evaporation of fluid at a higher rate than the combined areas ofinlet reservoirs cartridge 10 b towards theapertures 34. In this embodiment,material 33 is not required for the function of this device. - The movement of fluid through a microfluidic cartridge by differential evaporation at the inlet and outlet reservoirs is, provided that all evaporation areas are kept at the same temperature, only a function of the surface area of these evaporation areas. If the surfaces are liquid-filled, then the actual area differences determine the force driving the fluid movement. If the surfaces are a wetted porous material such as a filter paper, then the surface roughness also increases the effective surface area. The rougher a surface is, the more “evaporative force” it creates.
- The differential “evaporative force” can be enhanced by keeping the different evaporative areas at different temperatures, as evaporation is enhanced by increased temperature. For example, an inlet area at a low temperature, and an outlet area of the same size as the inlet area, but at a higher temperature, would create fluid movement towards the outlet.
- Alternatively, a magnetic material can be placed within
reservoir 20, and the liquids applied toports channels reservoir 20. These ferrofluids could also be used in combination with reagents and specimen samples to either push or pull these fluids through T-Sensor 12 by magnetic forces. -
FIG. 5 shows another alternative design for operating the T-Sensor ofFIG. 1 . In this embodiment, a liquid sample of reagent is applied to port 14 a ofcartridge 10 c while a liquid sample of specimen is applied to port 16 a.Channels channels Sensor 12 into terminatingreservoir 20.Channels Sensor 12. -
FIG. 6 is still another alternative embodiment for T-Sensor operation. In thiscartridge 10 d, T-Sensor 12 includes afirst pressure head 40 for receiving a reagent sample and asecond pressure head 42 for receiving a specimen sample. To operate T-Sensor 12, the cartridge is placed vertically and a sample of reagent is introduced intochannel 14 viahead 40 and a sample of specimen introduced intochannel 16 viahead 42. The hydrostatic pressure present by virtue of the orientation ofcartridge 10 d drives the liquids throughchannel 18 of T-Sensor 12 and intoreservoir 20. The velocity at which the liquids travel throughcartridge 10 d can be varied by tilting the cartridge from the vertical position. - The flow of fluids within
cartridge 10 d ofFIG. 6 can be significantly enhanced using a structural feature that uses the reservoir edges to improve the “wet-out” of the cartridge. Referring now toFIG. 13 ,cartridge 10 d includes pressure heads 40 and 42 which are coupled tochannels common channel 18.Channel 18 eventually connects to areservoir 20, which is preferably vented to the atmosphere external tocartridge 10 d via a ventingaperture 21.Connection 22 betweenchannel 18 andreservoir 20 is a right angle bend which is located at some distance frombottom wall section 23 andreservoir 20. -
FIG. 14 is an enlarged view of the connection betweenchannel 18 andreservoir 20. While the horizontal dimension of the channel mouth atconnection 22 may be narrow or wide,vertical dimension 24 must be large enough that the surface tension of a liquid 25 flowing withchannel 18 is inadequate to support a liquid drop. if this requirement is fulfilled within the structure ofcartridge 10 d, the liquid 25 entering reservoir forms a thin stream as shown at 26 from the bottom ofconnection 22 and flows down thewall 27 ofreservoir 20. By using this structure, pressure oscillations inchannel 18 that would occur as drops form and fall withinreservoir 20 is avoided, thus ensuring a smooth liquid flow. - Hydrostatically driven microfluidic circuits use gravity as their driving force. The pressure generated is a function of the difference in inlet and outlet liquid height level. This pressure is a constant for a given height difference, and generates a fluid flow in the microfluidic circuit. Flow speed and flow ratios for a given pressure are largely a function of the fluid resistance in these microchannels, and of the viscosity of the solutions. For example, in a given T-Sensor, the fluid flow ratio between the two fluids will depend on the viscosity ratio of the two fluids. Blood has a viscosity about 3-4.5 times greater than that of aqueous solutions. Therefore, blood will flow more slowly than an aqueous solution as the two streams flow along each other in a T-sensor channel. However, for a given hydrostatic pressure, the dividing line between the two streams will remain independent of a change of viscosity (i.e., for the same hydrostatic pressure, the dividing line will be at the center of the channel). The volumes that flow through the channel per time however, are a function of their viscosity, and higher viscosity solutions will flow at a lower volume flow rate. This will eventually cause the water levels of the two inlet streams to become different, since the low-viscosity fluid will drain more quickly. This change in water levels between the two inlet streams then would have an effect on the hydrostatic pressure, and the resulting flow patterns. This can easily be remedied by using comparably large volume pressure heads which change very little during the measurement time.
- This phenomenon is different from flow patterns in a volume-controlled flow situation (as is usual for syringe-pump positive displacement pumps). In this case, a constant volume flow rate will move the same amount of liquid per time through the channel. In case of different viscosities of sample and reagent, the center line will shift to the side of the lower-viscosity stream, as the higher viscosity stream flows more slowly.
- The advantages of pressure driven flow in T-Sensors is therefore that the position of the center line is independent of viscosity. This phenomenon can be used to simplify detection in these devices.
- One method to compensate for a change in flow speed due to a change in viscosity is to include a small “metering bubble” in the inlet channels. The time it takes to fill this bubble is proportional to the flow speed of each solution, which again is proportional to the viscosity of each solution.
- While hydrostatic pressure is a very constant source of power for microfluidic structures, it may be necessary at times for some types of structures to overcome some initial surface effects while filling a cartridge prior to allowing gravity or capillary forces to keep the flow constant and well controlled. A variety of methods for “jump-starting” the flow can be used: tapping on the inlets, using a syringe to either aspirate or press fluid into the disposable, using a “bubble pump”, or a variety of other processes.
- Microfluidic cartridges can also be surface-treated (for example, by a so-called Oxygen Plasma process) to create surfaces that can be more easily wetted by aqueous solutions. Such cartridges generally do not need to be “jump-started”, as the capillary forces draw fluids into these cartridges autonomously. By selective surface treatment, some areas of the cartridge can be filled, while others can create so-called surface tension valves, which require a certain amount of pressure to overcome before they wet.
- An alternate embodiment of the cartridge of
FIG. 6 is shown inFIG. 7 . In thiscartridge 10 e, avent passage 50 is connected toreservoir 20.Vent passage 50 includes a compressibleaspiration bubble pump 52 and a closure means 54. To operate T-Sensor 12 incartridge 10 e,aspiration bubble 52 is depressed while a reagent sample and a specimen sample are introduced into pressure heads 40,42. After pressure heads 40,42 are filled, closure means 54 is activated to sealvent passage 50 from atmosphere.Bubble 52 is then released causing the reagent and specimen to enter T-Sensor 12 viachannels reservoir 20. -
FIG. 8 shows yet another version of the cartridge of the present invention.Cartridge 10 f contains acompressible pressure bubble 60 which is connected toparts passages vent passage 50 connectsreservoir 20 to atmosphere. T-Sensor 12 incartridge 10 f operates as follows:bubble 60 is depressed, forcing air throughpassages reagent 14 a and specimen inport 16 a to enter T-Sensor 12 viachannels reservoir 20. -
Bubble 60 can alternatively contain a liquid in equilibrium with its gas phase; some liquids, such as alcohol, acetone, methanol, have a vapor pressure high enough at room temperature to provide a constant pressure source to drive liquids through T-Sensor 12. The pressure source will only cease once all the liquid inbubble 60 has been converted to the gas phase; until then, pressure will be constant, and only a function of temperature. - Another type of microfluidic device which can be readily adapted to manual operation is the H-Filter. The H-Filter structure is described in detail in U.S. Pat. No. 5,932,100, the disclosure of which is hereby incorporated by reference. Manually operated H-Filters can be used to separate components from particulate-laden samples such as whole blood, or to manufacture small quantities of chemicals.
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FIG. 9 shows a cartridge similar toFIG. 6 embodying the present invention in the form of an H-Filter. Cartridge 10 g contains afirst pressure head 40 for receiving a reagent sample and asecond pressure head 42 for receiving a specimen sample. An H-Filter 70 is coupled to pressure heads 40, 42 viachannels Filter 70 consists of achannel 72 which connectschannels separate reservoirs common vent 80. In the embodiment shown inFIG. 9 ,channel 72 of H-Filter 70 follows a serpentine path which assists in creating turbulence to enhance mixing; however,channel 72 can be straight, such aschannel 16 c shown in T-Sensor 12 c inFIG. 2 . - Referring now to
FIG. 9 , the operation of cartridge 10 g will now be described. A sample, such as whole blood, is inserted intopressure head 40, while an acceptor reagent, such as water or saline is inserted intopressure head 42. Two parallel laminar streams will flow throughchannel 72 as the liquids travel fromchannels separate reservoirs Filter 70.Reservoir 74 will then contain a sample solution with a reduced concentration of the extracted component, whilereservoir 76 contains the acceptor reagent containing the extracted reagent at a level of some fraction of its original concentration in the sample. The contents of bothreservoirs - It may be advantageous to provide the disposables pre-filled with reagents on the cartridge. Such reagents can be placed in inlet reservoirs, and sealed with a membrane, tape, or the like. Prior to the measurement, the user fills the sample inlet reservoir, and then removes the reagent seal. This process allows the reagents to start flowing down the channel. Alternative sealing methods may be surface-tension controlled orifices which require a certain initial pressure to overcome the surface effects, and to start flowing, or other types of manual or mechanical valves.
- By combining a flexible manual “bubble pump” (as shown in
FIGS. 7 and 8 ) with a one-way valve, fluids can be pumped in a closed circuit for a period of time. This may be advantageous when extracting or washing samples or reagents, and multiple passes through a microfluidic structure would increase the yield. - Mixing solutions in manually driven microfluidic circuits can be either diffusion-based in a laminar channel (as in H-Filters and T-Sensors), or quasi-turbulent. Several structures can be used to mix solutions in a quasi-turbulent fashion. Generally, such structures consist of a succession of corners, edges, zig-zag channels, or other features which increase the likelihood that laminar recirculation or turbulence can be generated in microchannels at the flow speeds available with a manually driven microfluidic circuit.
FIG. 10 shows the relationship between hydrostatic pressure and Reynolds number for a typical microfluidic mixing structure. A Reynolds number of 10 is usually sufficient to induce mixing. Turbulent or quasi-turbulent mixing is required for relatively large particles (Molecular weight of 1000 KD or more). Alternatively, bubble pumps can generate enough pressure to turbulently mix solutions in most microfluidic structures. - Other assay methods that lend themselves to manually driven microfluidic circuits are assays that use agglutination or sedimentation. For example, antibody-antigen complexes may either sediment into a microfluidic reservoir for detection or further processing, or they may form particles that intentionally get stuck in small microfluidic features such as orifices. The presence or absence of these complexes in particular parts of the microstructures can serve as an indicator for the presence, absence, or quantity of an analyte. This could be used to develop a method for blood typing.
- A simple detection method for analyzing the results of an assay performed is a microfluidic format according to the present invention is shown in
FIGS. 15-17 . Referring now toFIG. 15 , a basic T-Sensor device 12 is shown having anindicator port 14 a and ananalyte port 16 a.Port 14 a is connected tomain channel 18 by asample channel 14, whileport 16 a is connected to channel 18 by ananalyte channel 16 a. InFIG. 15 , a high concentration analyte is loaded intoport 16, and when T-Sensor 12 is operated with an indicator solution withinport 14, a diffusion pattern forms as shown at 90. InFIG. 16 , a low concentration analyte is loaded intoport 16, and adifferent diffusion pattern 92 is generated. - At some point along
channel 18, the reaction between the analyte and indicator will become sufficiently intense to be seen visually. This point inchannel 18, which is located some distance fromchannels channel 18. Optical aids, such as a magnifying lens, colored filter layer, or slit may aid on the manual visual interpretation of the concentration. - An example of a device for simple quantitation of a microfluidic device which requires no external instruments is shown in
FIG. 17 . Referring now toFIG. 17 , a convoluted T-Sensor 12e having ports channels main channel 18 a upon which aviewing window 100 has been inserted. In addition, achart 102 is placed near T-Sensor 12 e which contains indicia representative of different concentrations of the desired analyte. During operation of T-Sensor 12 e, quantitation is achieved by interpreting the point at which a visible reaction has occurred at the interface between the sample and indicator. The only portion ofChannel 18 visible is seen throughviewing window 100. In this embodiment, the analyte may be at a 4+ to 5+ amount (1+ being low, 10+ being high) because in the 6+view area ofwindow 100, there is barely an reaction visible. - This embodiment is aimed at providing a quantitative assessment of analyte concentration in a format that is compatible with manual performance and visual readout. This format is particularly appropriate for use with kinetic assays—in which product builds up with time—since time in a microfluidic channel corresponds to geographic distance. Examples of kinetic assays are enzyme assays, and some slow finding reactions, such as some antibody-antigen reaction. However, this technique may also work with “fast” reactions, because visual interpretation incorporates both intensity of color and “thickness” of color at the interface.
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FIG. 18 shows a microfluidic device according to the present invention which joins two fluid streams in a manner which prevents the formation of air bubbles within the channels that may hamper the performance of the device. Referring now toFIG. 18 , a pair ofreservoirs microfluidic outlet channel 18 by a pair ofinlet channels channel 18 is tapered such that it is wider atsection 18 a where it connects tochannels Channel 14 connects toreservoir 14 a at 110, whilechannel 16 connects toreservoir 16 a at 112. - When
reservoirs channels channel 18, because typically the liquid in one channel flows insection 18 a ofchannel 18 before the liquid in the other channel breaks through the surface tension barrier where the channel meets the bottom of the reservoir. As shown inFIG. 18 , fluid fromreservoir 14 a has already reachedchannel 18, as shown at 114, whereas the fluid inreservoir 16 a is still trapped by the surface tension of the liquid-gas interface wherereservoir 16 a meetschannel 16, as shown at 112. - To avoid trapping an air bubble in this microfluidic device, two constraints must be addressed in the design of the microfluidic circuitry. First, the
outlet channel 18 must be large enough to contain the volume ofinlet channel 14 fromreservoir 14 a without trapping the air inchannel 16. Second, the pressure differential between the pressure inoutlet channel 18 and the pressure at 110, which is due to the fluid resistance to flow withinchannel 14, must be greater than the pressure differential between the pressure inoutlet channel 18 and the pressure at 112, which is due to the surface tension of the gas-liquid interface at 112. This is accomplished by narrowing the width ofchannel 16 as needed for the surface tension characteristic of the liquid and gas pair. - Surface tension valves are based on the difference in resistance contained in unwetted orifice as compared to a wetted orifice. These valves are considered “single use” valves, as once they are wetted, they behave essentially like a low resistance flow channel (dynamic resistance); however, these valves present enough resistance (static resistance) to block the fluid flow, even if some force is applied to them such as pressure, capillary forces, or hydrostatic pressure. Once this static force is overcome by a “breaking force,” fluid will flow through the valve.
- Resistance of the
inlet channels - In operation, as the cartridge is being filled, only the resistance of one of the
inlet channels reservoirs outlet channel 18. Surface tension valves typically consist of an orifice, a channel terminating in sharp edges, or other structures which create a high surface tension. Alternatively, the surface of a channel can be coated with a specific material in the valve area, thereby increasing the surface tension resistance at that point. However, the actual resistance exhibited by these valves depends to a large extent on the exact dimensions and surface properties; thus, manufacturing tolerances can have a significant impact on the accuracy of these valves. - One method of improving the reliability of surface tension valves would be to provide multiple redundant surface tension valves in parallel rather than a single valve. Although the multiple valves will vary statistically in resistance, but the average of the group will be close to that of a single valve. For example, by placing multiple small orifices between two channels, the same approximate surface tension can be achieved each time.
FIG. 11 shows the use of multiple orifices within a channel to exhibit this principle. - Finally, an alternative design for a surface tension valve would provide a maximum breaking resistance, along with a minimum breaking resistance, for the valve.
- The principles of the present invention can be applied to many other types of products. For example, a cartridge containing a microfluidic device as described can be used as science kits, such as a miniature chemical laboratory, for educational purposes. Another use could be as a novelty device that uses fluid flow to visualize specific patterns, such as company logos, names, signatures, and the like on a small plastic card roughly the size of a standard credit card.
- While the invention has been shown and described in terms of several preferred embodiments, it will be understood that this invention is not limited to these particular embodiments and that many changes and modifications may be made without departing from the true spirit and scope of the invention as defined in the appended claims.
Claims (16)
1. A device for moving fluids through a microfluidic channel, comprising:
a microfluidic channel having an inlet and an outlet;
a fluid contained within said channel;
and an absorbent material coupled to said outlet of said channel,
whereby when said fluid within said channel initially contacts said absorbent material, a driving force is created which moved said fluid through said channel to said outlet.
2. The device of claim 1 , wherein said fluid creates a moving fluid front across said absorbent material as said fluid contacts said material.
3. The device of claim 2 , wherein said absorbent material is shaped such that the flow speed of said moving fluid front across said material is controlled by the shape of said material.
4. The device of claim 3 , wherein said absorbent material comprises a triangular shape and is positioned such that said moving fluid front expands as fluid is absorbed, hereby increasing the driving force as fluid moved through said channel.
5. A device for providing a constant flow within a microfluidic channel, comprising:
a fluid reservoir;
a first microfluidic channel connected to said reservoir;
and a first passageway for coupling said reservoir to said first channel,
whereby said first passageway is sized such that fluid entering said reservoir from said first channel flows in a smooth constant stream.
6. A device for providing a continuous flow within a microfluidic channel, comprising:
a fluid reservoir having a top surface and a bottom surface;
a first microfluidic channel connected to said reservoir;
and a first passageway for coupling said first channel to said reservoir at a position between said top surface and said bottom surface,
wherein said first passageway is sized such that fluid entering said reservoir from said first channel flows in a smooth, continuous stream.
7. A device for providing a visual indication of the concentration of an analyte in a microfluidic channel, comprising:
a microfluidic detection channel having an inlet and an outlet;
an indicator channel coupled to said detection channel at said inlet;
an indicator channel coupled to said detection channel at said inlet apposite said indicator channel;
a first fluid introduced through said indicator channel into said detection channel toward said outlet;
indicating means representative of second fluid concentration located in proximity to said detection channel,
wherein when said first and second fluids flow within said detection channel toward said outlet, a diffusion pattern is formed indicative of the concentration of said second fluid within said detection channel such that the diffusion pattern may be compared to said indicating means to determine concentration within said detection channel.
8. The device of claim 7 , wherein said indicating means further includes a template having a plurality of viewing windows such that said diffusion pattern within said indicator channel visible within said windows may be compared to said indicating means to determine concentration within said channel.
9. A microfluidic device for joining two or more fluid streams, comprising:
a first channel having an inlet opening and an outlet opening;
a second channel having an inlet opening and an outlet opening;
and a main microfluidic channel having an inlet coupling region for coupling said outlet openings of said first and second channels to said main channel,
wherein said coupling region is sized such that fluid entering said region from either of said first or second channel outlet openings enters said main microfluidic channel without blocking said outlet opening of said other channel.
10. The device of claim 9 wherein said first and second channels are sized such that a substantial portion of the fluid contained within said channels can enter said coupling region without blocking said outlet opening of said other channel.
11. The device of claim 10 wherein said outlet openings of said first and second channels are separated by at least one diameter of one said outlet openings.
12. The device of claim 9 wherein said inlet opening of said first channel is connected to a first reservoir and said inlet opening of said second channel is connected to a second reservoir.
13. The device of claim 12 , wherein said inlet openings of said first and second channels comprise surface tension valves.
14. The device of claim 13 , wherein the static resistance of said surface tension valves is lower than the dynamic resistance within said first and second channels.
15. The device of claim 12 , further comprising driving means, internal to said first and second reservoirs, for driving fluid through said first and second channels into said main microfluidic channel.
16. A device for providing static resistance to flow in a microfluidic system, comprising:
an inlet channel;
an outlet channel;
and a plurality of orifices, each having essentially the same dimensions, located in parallel between said inlet and outlet channels,
whereby said orifices provide a high static resistance than a single orifice but a substantially lower dynamic resistance to flow.
Priority Applications (1)
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- 2000-10-06 US US09/684,094 patent/US6743399B1/en not_active Expired - Lifetime
- 2000-10-06 WO PCT/US2000/027898 patent/WO2001026813A2/en active Application Filing
-
2004
- 2004-04-08 US US10/821,267 patent/US20050045479A1/en not_active Abandoned
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
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US6743399B1 (en) * | 1999-10-08 | 2004-06-01 | Micronics, Inc. | Pumpless microfluidics |
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US10168322B2 (en) * | 2004-07-09 | 2019-01-01 | Church & Dwight Co., Inc. | Electronic analyte assaying device |
US7731910B2 (en) | 2005-08-05 | 2010-06-08 | Hewlett-Packard Development Company, L.P. | Microfluidic mixing assembly |
US20070028969A1 (en) * | 2005-08-05 | 2007-02-08 | Bovd Patrick V | Microfluidic mixing assembly |
US20070215528A1 (en) * | 2006-03-16 | 2007-09-20 | Hayenga Jon W | Cantilevered coaxial flow injector apparatus and method for sorting particles |
US7569789B2 (en) | 2006-03-16 | 2009-08-04 | Visiongate, Inc. | Cantilevered coaxial flow injector apparatus and method for sorting particles |
US10066977B2 (en) | 2009-01-26 | 2018-09-04 | Canon U.S. Life Sciences, Inc. | Microfluidic flow monitoring |
US9404152B2 (en) | 2009-01-26 | 2016-08-02 | Canon U.S. Life Sciences, Inc. | Microfluidic flow monitoring |
US20130206250A1 (en) * | 2010-07-05 | 2013-08-15 | Tsinghua University | Bubble-based microvalve and its use in microfluidic chip |
US20120024708A1 (en) * | 2010-08-02 | 2012-02-02 | The Regents Of The University Of California | Single-sided continuous optoelectrowetting (sceow) device for droplet manipulation with light patterns |
US9533306B2 (en) * | 2010-08-02 | 2017-01-03 | The Regents Of The University Of California | Single sided continuous optoelectrowetting (SCEOW) device for droplet manipulation with light patterns |
US20180001231A1 (en) * | 2014-01-29 | 2018-01-04 | General Electric Company | Devices for separation of particulates, associated methods and systems |
US10518196B2 (en) * | 2014-01-29 | 2019-12-31 | General Electric Company | Devices for separation of particulates, associated methods and systems |
US10124333B2 (en) | 2014-06-10 | 2018-11-13 | Reolab Inc. | Discrete elements for 3D microfluidics |
WO2015191723A1 (en) * | 2014-06-10 | 2015-12-17 | University Of Southern California Usc | Discrete elements for 3d microfluidics |
US20190234842A1 (en) * | 2016-10-06 | 2019-08-01 | Ventana Medical Systems, Inc. | System, method and kit for sample preparation |
US20210252502A1 (en) * | 2019-06-10 | 2021-08-19 | Instant Nanobiosensors, Inc. | Microfluidic detection unit and fluid detection method |
US11944970B2 (en) * | 2019-06-10 | 2024-04-02 | Instant Nanobiosensors, Inc. | Microfluidic detection unit and fluid detection method |
Also Published As
Publication number | Publication date |
---|---|
WO2001026813A3 (en) | 2001-11-22 |
US6743399B1 (en) | 2004-06-01 |
WO2001026813A2 (en) | 2001-04-19 |
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